Oxidized zirconium on a porous structure for bone implant use

ABSTRACT

A composition, a medical implant constructed from the composition, and a method of making the composition are described. The composition is a composite material, comprising a porous, reticulated, open cell network having at least part of its surface coated with blue-black or black oxidized zirconium.

TECHNICAL FIELD

This application is a divisional application of, and claims priority to,U.S. application Ser. No. 10/737,568, filed on Dec. 16, 2003.

This invention relates to composite materials having an open cellstructure onto which one or more other materials are deposited. Thecomposite material is particularly applicable to bone-implant uses, butmay also be used in other applications.

BACKGROUND OF THE INVENTION

There is an ongoing need for replacement materials for cancellous bone,particularly where such materials are cell and tissue receptive. It isdesirable that cancellous bone replacement materials provide a porousframework allowing for revascularization as well as new bone growth, andone which provides a compatible site for osteoprogenitor cells and bonegrowth-inducing factors. Grafting, however, requires surgery to obtainnatural material, and a viable substitute synthetic material isdesirable. Thus, a suitable, synthetic cancellous bone replacementmaterial would be beneficial to these ends. In order to mimic thebehavior of cancellous bone grafts, it is expected that the physicalcharacteristics of this material should be reproduced in the syntheticmaterial. Thus, any such material should be strong, biocompatible,should match the biomechanical requirements and performance of thenatural material and have a porous framework which promotesrevascularization and bone regrowth. For these latter two processes tooccur, it is critical that bone ingrowth into and onto the replacementmaterial occur to an appreciable extent.

The voids and interstices of a porous material provides surfaces forbone ingrowth, thereby providing ideal skeletal fixation for thepermanent implants used for the replacement of bone segments lost due toany number of reasons, or in total joint prostheses. The implants may beconventional total joint replacements such as artificial hip, knees,etc., or partial joint replacements such endoprostheses components. Anumber of characteristics are known in the art to be important. Theseinclude porosity, biological compatibility, intimate contact with thesurrounding bone, and adequate early stability allowing for boneingrowth. The ideal porous replacement material should have goodstrength, especially good crack and impact resistance and a compliancecomparable to that of bone. The material should be ideally be amenableto the easy and simple manufacture of implants of precise dimensions,and permit the fabrication of either thick or thin coatings on thematerials.

One important requirement for successful ingrowth is that the implantmaterial be placed next to healthy bone. In fact, the presence of bonewithin the implant demonstrates the osteoconductive, or bone-growthpromoting properties of the porous structure of the implant when it isplaced in physical contact with healthy bone tissue. Initially, thecells that interface the implant convert to bone, then the front ofregenerated bone progresses into the implant.

There have been numerous efforts to develop and manufacture syntheticporous implants having the proper physical properties required topromote bone ingrowth. Implants with porous surfaces of metallic,ceramic, polymeric, or composite materials have been studied extensivelyover the last two decades.

The most commonly used substance for porous biomaterials is calciumhydroxyapatite (HA), which is the largest chemical constituent of bone.Other nonmetallic materials frequently used in porous form for implantsinclude the ceramics tricalcium phosphate (TCP), calcium aluminate, andalumina, carbon; various polymers, including polypropylene,polyethylene, and polyoxymethylene (delrin); and ceramic-reinforcedor-coated polymers. Unfortunately, ceramics, while strong, are verybrittle and often fracture readily under loading; and polymers, whilepossessing good ductility, are extremely weak. The very nature of thesematerials can restrict their clinical dental and orthopedicapplications.

Metals, on the other hand, combine high strength and good ductility,making them attractive candidate materials for implants (and effectivelythe most suitable for load-bearing applications). Many dental andorthopedic implants contain metal, most often titanium or various alloyssuch as stainless steel or vitallium (cobalt-chromium-molybdenum).Ceramic-coated metals are also used, typically HA or TCP on titanium.Additionally, a large variety of metals are used internally inbiomedical components such as wire, tubing, and radiopaque markers.

Many existing metallic biomaterials, however, do not easily lendthemselves to fabrication into the porous structures that are mostdesirable for bone implants. These materials (e.g. stainless steel,cobalt-based alloys) exhibit the necessary properties andbiocompatibility as long as only a smooth, bulk shape in ametallurgically perfect state is needed. The machining or othertreatment needed to obtain a porous or surface-textured shape forinterlocking with skeletal tissue can have a detrimental effect on theproperties and biocompatibility, and can even result in materialfailure. For example, the hexagonal crystal structure of titanium makesit susceptible to cracks and fractures, as has been seen in the case ofdental implants. Some porous metallic materials (e.g. flame- orplasma-sprayed titanium, porous sintered powder metallurgy materials) donot match the structure of cancellous bone sufficiently well to ensuresuccessful ingrowth and integration. Also, most metals and alloyscurrently in use are subject to some degree of corrosion in a biologicalenvironment. Finally, the high densities of metals can make themundesirable from a weight standpoint.

A significant step in the improvement of porous implants occurred withthe introduction of a reticulated open cell carbon foam is infiltratedwith tantalum by the chemical vapor deposition (CVD) process that wasdescribed in U.S. Pat. No. 5,282,861. The '861 patent taught a newbiomaterial that, when placed next to bone or tissue, initially servesas a prosthesis and then functions as a scaffold for regeneration ofnormal tissues. The '861 material fulfills the need for an implantmodality that has a precisely controllable shape and at the same timeprovides an optimal matrix for cell and bone ingrowth. The physical andmechanical properties of the porous metal structure can be specificallytailored to the particular application at hand. Although it is expectedto have its greatest application in orthopedics, this new implantmaterial offers the potential for use in alveolar ridge augmentation,periodontics, and other applications. As an effective substitute forautografts, it will reduce the need for surgery to obtain those grafts.

The open cell structure of the prior art is made from tantalum. Most ofthe current orthopaedic implants are made from titanium or cobaltchromium alloy, or more recently from zirconium alloy. The use oftantalum along with the titanium or cobalt chromium alloy poses apossibility of galvanic interaction, the effects of which are currentlynot known. A porous structure that is made from an alloy which iscurrently used in the orthopaedic industry will be a great advantage asit can be safely incorporated with the existing alloying system.However, the open cell structures of the prior art suffered from a lackof strength for certain implant applications. An improvement in thestate of the art of porous implant structures may be achieved if thestrength of the structure can be improved. This would facilitate itswidespread use in both conventional implants such as hip, knees, etc.,as well as in specialty applications such as replacements for vertebralbodies that make up the spinal

column. BRIEF SUMMARY OF THE INVENTION

The present invention is directed to a composition, a medical implantconstructed from the composition, and a method of making thecomposition. The composition is a composite material, comprising aporous, reticulated, open cell network having at least part of itssurface coated with blue-black or black oxidized zirconium. Thesubstrate material comprising the open cell network may comprise anymaterial having suitable strength for a given application. Non-limitingexamples include metal, carbon foam, or polymer material.

In one aspect of the present invention there is a composite materialcomprising a reticulated open cell substrate formed of a substantiallyrigid foam material, said substrate comprising an interconnectingnetwork having interconnected continuous channels, and a surface layerof blue-black or black oxidized zirconium.

In one embodiment of the composite material, the surface layersubstantially covers said interconnecting network. In another embodimentof the composite material the foam material is carbonaceous material. Inyet another embodiment of the composite material, the carbonaceousmaterial is graphite. In another embodiment of the composite material,the foam material is a polymer material. In one embodiment, the polymermaterial comprises polyethylene. In another embodiment, the polymermaterial comprises polypropylene. In another embodiment, the polymermaterial comprises both polypropylene and polyethylene. In anotherembodiment of the composite material, the foam material is selected fromthe group consisting of ceramic, metal, and metal alloy. In anotherembodiment of the composite material, the material further comprises asecond substrate material, the second substrate material being bonded tosaid open cell substrate.

In another aspect of the present invention there is a method of making acomposite material comprising the steps of providing a material having areticulated open cell structure, depositing a layer of zirconium orzirconium alloy onto said substrate; and, oxidizing said layer toblue-black or black oxidized zirconium.

In one embodiment of the method, the step of depositing compriseschemical vapor deposition or physical vapor deposition or both. Inanother embodiment of the method, the step of oxidizing comprisesoxidizing using air, steam, or water oxidation or any combinationthereof. In yet another embodiment of the method, the step of oxidizingcomprises oxidizing in a furnace having an oxygen-containing atmosphere.

In another aspect of the present invention there is a method of making acomposite material comprising the steps of providing a material having areticulated open cell structure, physically constructing a layer ofzirconium or zirconium alloy onto said substrate, and oxidizing saidlayer to blue-black or black oxidized zirconium.

In one embodiment of the method, the step of physical constructioncomprises direct casting. In another embodiment of the method, the stepof physical construction comprises building a diffusion-bonded layer.

In another aspect of the present invention there is a medical implantcomprising a composite material, said composite material comprising areticulated open cell substrate formed of a substantially rigid foammaterial said substrate comprising an interconnecting network havinginterconnected continuous channels, and a surface layer of blue-black orblack oxidized zirconium.

In a specific embodiment of the medical implant, the medical implant isa hip prosthesis. In another embodiment, the medical implant is a kneeprosthesis. In another embodiment, the medical implant is a spinalprosthesis. In yet another embodiment, the medical implant is a spinalprosthesis and the spinal implant is a vertebral body. In anotherembodiment, the medical implant is a bone graft.

The foregoing has outlined rather broadly the features and technicaladvantages of the present invention in order that the detaileddescription of the invention that follows may be better understood.Additional features and advantages of the invention will be describedhereinafter which form the subject of the claims of the invention. Itshould be appreciated that the conception and specific embodimentdisclosed may be readily utilized as a basis for modifying or designingother structures for carrying out the same purposes of the presentinvention. It should also be realized that such equivalent constructionsdo not depart from the invention as set forth in the appended claims.The novel features which are believed to be characteristic of theinvention, both as to its organization and method of operation, togetherwith further objects and advantages will be better understood from thefollowing description when considered in connection with theaccompanying FIGURES. It is to be expressly understood, however, thateach of the FIGURES is provided for the purpose of illustration anddescription only and is not intended as a definition of the limits ofthe present invention.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, reference isnow made to the following descriptions taken in conjunction with theaccompanying drawing, in which:

FIG. 1 is a schematic illustration of an open cell structure of thepresent invention.

DETAILED DESCRIPTION OF THE INVENTION

As used herein, “a” and “an” include both the singular and the pluraland mean one or more than one.

New materials are enabling the design of innovative, and increasinglybiocompatible, replacements for damaged human tissues. In the presentinvention, reticulated open cell carbon foam is infiltrated withzirconium or zirconium alloy by any of a number of techniques known inthe art, including any deposition-based techniques known in the art suchas, for example, chemical vapor deposition (CVD), physical vapordeposition (PVD), and arc deposition. The zirconium or zirconium alloyis then oxidized to a blue-black or black oxidized zirconium, which hasthe optimum combinations of the beneficial properties of ceramics andmetals while suffering little, if at all, from the disadvantages ofeither. Additionally, physical construction of the composition isanother possible route and such techniques include, for example, directcasting or building a diffusion-bonded layer.

The porous substrate material may be any material having a porous,open-cell network. Carbon foam, such as that disclosed in U.S. Pat. No.5,282,861, hereby incorporated by reference as though full disclosedherein, is one example. Other possible substrate materials includepolymeric materials, metallic materials including metal alloys, andceramic materials. The only requirement of the substrate is that itpossess an open-cell porous network and have sufficient strength as toimpart appropriate structural integrity to the resulting composition. Itpreserves the structural strength of conventional implants, yet it islightweight relative to the same conventional implants. These poroussubstrates may be fabricated by any suitable techniques. Some examplesinclude, but are not limited to, (i) polymer foams that are fabricatedby introducing gas bubbles into the liquid monomer or hot polymer andformed into a reticulated network, (ii) metal foams that are fabricatedby a powder metallurgy route and may or may not include selectiveleaching of one or more components, (iii) metal or ceramic foams thatare fabricated by coating an open-cell polymer foam substrate usingvapor deposition processes (chemical or physical) or electrochemicaldeposition processes, and (iv) metal or ceramic foams that are producedby plasma or flame spray deposition on polymer foams.

FIG. 1 is a schematic illustration of an open cell structure (1) of thepresent invention with deposited oxidized zirconium or zirconium alloy.Open spaces (4) are interconnected by structural material (7). Thestructure thus comprises interior surface (11) (the surfaces of theinternal cells and interconnecting channels) and exterior surface (15)(the outward-facing surfaces). In the embodiment illustrated in FIG. 1,the surfaces of the open cells comprise blue-black or black oxidizedzirconium (designated by cross-hatched regions (4) and (11)). Asdiscussed below, other embodiments are within the scope of theinvention, such as the embodiment wherein all surfaces (both theexterior surfaces as well as those of the open cells) compriseblue-black or black oxidized zirconium. While initial contact withsurrounding bone or tissue would primarily occur through the exteriorsurface of the structure, bone and tissue ingrowth and on-growth wouldresult in physical contact between the interior surface and surroundingbone and tissue also. With the variables available in both the materialsand the fabrication process, it is possible to obtain the simultaneousoptimization of multiple properties (e.g. strength, stiffness, density,weight) for the given application of substitution for bone.

A major advantage of the open cell structure described herein is that itis readily shapeable to nearly any configuration, simple or complex,simply by shaping the substrate material prior to application of thesurface material. This facilitates exact contouring of the implant forthe specific application and location; precise placement is enhanced andbulk displacement is prevented. Additionally, it appears that any finalshaping/trimming needed at surgery can be accomplished on the finaldevice using conventional dental or orthopedic equipment available atthe time of surgery.

The optimal conditions for fracture healing and long-term stability canbe met if an implant can be designed allowing for motionlessness alongall the interfaces necessary for a stable anchorage, thereby excluding(to the greatest extent possible) all outside influences on theremodeling process and allowing the local stress/strain field tocontrol.

Following implantation and initial tissue ingrowth, the foam devicestays where it is placed without retention aids, a reflection of precisecontouring and the rapid ingrowth of fibrovascular tissue to preventdislodgement. The binding between bone and implant stabilizes theimplant and prevents loosening. These implants thus will not need to beheld in place by other means (e.g. sutures or cement); rather, thegrowth of a natural bone-to-bone seal is encouraged by the nature of theimplant itself. Tissue ingrowth would not be a contributing factor todevice retention for a period following implantation, however, until asubstantial amount of ingrowth had occurred

In one embodiment, a carbon foam substrate is infiltrated by chemicalvapor deposition (CVD). The resulting lightweight, strong, porousstructure, mimicking the microstructure of natural cancellous bone, actsas a matrix for the incorporation of bone or reception of cells andtissue. The pores of the matrix are connected to one another to formcontinuous, uniform channels with no dead ends. This intricate networkof interconnected pores provides optimal permeability and a high surfacearea to encourage cell and tissue ingrowth, vascularization, anddeposition of new bone.

The composite material may also be formed by physical vapor deposition.Alternatively, physical construction of the composition is anotherpossible preparatory route and such techniques include, for example,direct casting or building a diffusion-bonded layer. These and othermethods, which are known to those of skill in the art, are also part ofthe present invention.

The resulting composition is an exceptional biomaterial that, whenplaced next to bone or tissue, initially serves as a prosthesis and thenfunctions as a scaffold for regeneration of normal tissues. It satisfiesthe need for an implant modality that has a precisely controllable shapeand at the same time provides an optimal matrix for cell and boneingrowth. Additionally, the physical and mechanical properties of theporous metal structure can be specifically tailored to the particularapplication at hand. This new implant offers the potential for use inalveolar ridge augmentation, periodontics, and orthognathicreconstruction. As an effective substitute for autografts, it willreduce the need for surgery to obtain those grafts. It is useful inorthopedic applications as well.

The present invention may also be used for tooth replacement because ofthe ability to induce tissue and bone growth even in the face of mildlyinfectious conditions. For example, an artificial tooth can be joined toan open cell tantalum stem and positioned in an appropriately sized holein the jaw. The gum is allowed to rest against the artificial tooth andsome of the stem to form a seal.

Oxidized zirconium is chosen as the surface material due to its highstrength and high wear resistance. The oxidized zirconium surface of thecomposition of the subject invention is also useful in providing abiocompatible, inert ceramic barrier between the substrate and any bodyfluids which may otherwise come into contact with the substratematerial. Thus, since the oxidized zirconium surface is not prone toionization and wear-induced corrosion, both the life span and thebiocompatibility of the implant composition are enhanced.

Additionally, the natural in situ formation of an oxidized zirconiumsurface from the presence of zirconium in the substrate metal involvesoxygen diffusion into the substrate below the oxide coating. This ishelpful when the substrate comprises metal or metal alloy. Oxygen, analloying constituent in zirconium, increases the strength of the metalsubstrate, particularly the fatigue strength. Resistance to fatigueloading is paramount in many implant applications. Thus, not only doesthe formation of the oxidized zirconium surface improve wear, friction,and corrosion resistance, it also improves the mechanical integrity ofthe implant device from a strength standpoint.

Cancellous, or spongy, bone is composed of a porous space-framestructure formed of open spaces defined by interconnected trabeculae,oriented along lines of principal stresses. At the microstructurallevel, the trabeculae are composed of layers of lamellar bone.Cancellous bone has anisotropic mechanical properties, i.e. differentstructural behavior along different orientations. Along the axis of themajor channels, cancellous bone exhibits elastic behavior with suddenbrittle failure at ultimate load in tension. When loaded with a tensileforce whose line of action is skewed with respect to the channel axis ofthe bone, the stress-strain curve is parabolic with plastic deformationand greater energy absorption. It is therefore stiffer (has highertensile and compressive moduli) but fails at a lower strain when loadedparallel to the predominant spicular direction than when loaded in otherdirections. These properties are important because they serve to absorbshock and distribute load in the vicinity of the articular surfaces ofjoints.

Any material to be used as a substitute for cancellous bone musttherefore allow elastic deformation and load distribution. In addition,the material must not produce load concentrations, particularly ifplaced close to the underlying surface of articular cartilage, whichmight increase the local stresses on the articular surface and lead towear and damage of the surface.

Materials for osseous, or bone, implants must be rigid andstress-resistant, while avoiding self-concentration of stresses thatresult in stress shielding. Also, osseous implants should ideally residein the bone without interfering with bone remineralization, the naturalprocess by which the body replenishes bone. The implant should be ableto be precisely shaped and placed for optimal interface and performance.Finally, non-resorption would be a beneficial quality for implants usedin load-bearing applications, and/or those in which complete boneingrowth is not possible.

Completeness of the interconnectivity of a porous implant helps toimprove performance. This is so because constrictions between pores andisolated, deadend pockets can limit vascular support to ingrowingtissues; ischemia of the ingrowing bone cells results in failure of theimplant. Incomplete vascularization or a reduction in the neovascularityalso makes an implant increasingly vulnerable to bacterial colonization.Implants lacking completely interconnected porosity can also result inaberrant mineralization, stress shielding, low fatigue strength, and/orbulk displacement.

The open cell metal structure of the present invention offers highlyinterconnected, three-dimensional porosity that is uniform andconsistent, a structure exceptionally similar to that of naturalcancellous bone. In this way it is superior to other porous metallicimplant materials, whose “porosity” is artificially produced via someform of surface treatment that does not result in a truly complete, openporosity. Examples of these methods include macroscopic porous coatings(e.g. metal microspheres or wires sintered or otherwise attached to abulk surface); microscopic surface porosity (e.g. metal powder particlesflame- or plasma-sprayed onto a bulk surface); and controlled surfaceundulations machined into a bulk surface.

Although certain porous ceramic materials do offer full porosity (e.g.the replamineform process for hydroxyapatite), they have propertiesinferior to metals as discussed previously. The open cell metalstructure is osteoconductive, like other porous implants.

Allowing full mineralization is another extremely important propertyrequired of bone substitute materials. The highly organized process ofbone formation is a complex process and is not fully understood. Thereare, however, certain prerequisites for mineralization such as adequatepore size, presumably larger than 150 μm with interconnect size in therange of 75 μm. A pore diameter of 200 μm corresponds to the averagediameter of an osteon in human bone, while a pore diameter of 500 μmcorresponds to remodeled cancellous bone. The open cell metal structuresof the present invention can be fabricated to virtually any desiredporosity and pore size, and can thus be matched perfectly with thesurrounding natural bone in order to provide an optimal matrix foringrowth and mineralization. Such close matching and flexibility aregenerally not available with other porous implant materials.

One concern with an implant must be the potential for stress shielding.According to Wolff's law, bone grows where it is needed (that is, wherethere is a stress). Stress on a bone normally stimulates that bone togrow. With an implant, it is primarily the stress/strain field createdin the tissue around an implant that controls the interface remodeling.Stress shielding occurs when an overly stiff implant carries stressesthat were previously applied to the bone in that area; it can result ininhibition of mineralization and maturation of the ingrowing bone,and/or the resorption of existing natural bone.

An implant, then, should ideally distribute stresses throughout itsstructure, the ingrowing bone, and the surrounding bone in order toavoid bone resorption and weakening caused by stress shielding. Becausemetals are stronger than natural bone, this would seem to be a concernwith a metallic implant in that the implant would itself focus and beardirectly the majority of local loads and stresses that would ordinarilybe placed on the bone, thus depriving both the existing and new bone ofthose forces which, in effect, help keep it at optimal strength.

The unique structure and properties of the open cell metal structures ofthe present invention, however, avoid this drawback altogether. Thedeposited thin films operate as an array within the porous metal body,contributing their exceptional mechanical properties to the structure atlarge. One result of this effect is that imposed loads are distributedthroughout the body. In the case of a open cell metal bone implant,stresses are distributed into both the ingrowing new bone and thesurrounding existing bone as well, thereby providing both the old andnew bone with the normal, healthy forces they require.

In fact, with the ability to finely tailor the open cell metalstructure's properties during the fabrication process, an implant can bedesigned to distribute stresses in a given direction(s), depending onthe needs of the specific application at hand. The bonding ofregenerated bone to the implant also helps to transfer stresses directlyto the bone in and around the implant; this sharing of biofunction is aconsequence of the composite nature of the implant/bone structure. Theadvantage of these metal structures over other porous implant materialsis especially strong in this area. Ceramics lack sufficient mechanicalproperties to begin with, and no current implant material, eitherceramic or metallic, possesses the unique properties of the metalstructure as described here.

In the present invention, useful refractory structures are preferablymade by deposition techniques the chemical vapor deposition and physicalvapor deposition of a small amount of zirconium or zirconium alloy intoa reticulated (porous) vitreous structure. Preferably, this is carbonfoam, but may be any other material having an open cell, porous network.The density of the resultant body is purposely maintained atsubstantially below full density, resulting in a structure withextremely favorable properties. On preferred embodiment involves the useof a low-density carbon foam, which is infiltrated with the desiredmaterial by CVD to provide uniform thin films on all ligaments. Thesethin films provide exceptional strength and stiffness to the ligaments,with the expenditure of very little weight. Thin CVD films can providemuch higher mechanical properties than can bulk materials. Suchquasi-honeycomb materials have remarkably high specific strength andstiffness.

This process does not endeavor to densify the body fully, although it ispossible to do so, and useful parts can be so fabricated. In the presentinvention, thin films are located on the surfaces of the open cell,porous substrate, taking advantage of the apparent unusual mechanicalproperties of the thin films. Using a porous carbon with extremely highporosity and small pore size takes advantage not only of the propertiesof thin films, but of short beams as well.

It is permissible that the structural integrity of the fabricatedstructure is provided by the deposited thin films themselves, ratherthan by the open cell porous substrate. These films may have much highermoduli of elasticity than do the substrate materials. Because thedeposited films are so thin and short, they show great strength, notunlike the high strength experienced in very fine fibers or filaments.Their support of the mechanical load ensures that failure does not occurin the substrate material.

The substrate material may be carbon foam, a polymer such a polyethyleneor polypropylene. The material may also be metal or ceramic. The onlyrequirement is that the substrate possess a reticulated, open cell,porous network.

The reticulated, open cell, porous network is infiltrated by zirconiummetal or a zirconium alloy. The zirconium metal or zirconium alloy isthen oxidized to blue-black or black oxidized zirconium. The resultinglightweight, strong, porous structure, mimicking the microstructure ofnatural cancellous bone, acts as a matrix for the incorporation of boneor reception of cells and tissue. The pores of the matrix are connectedto one another to form continuous, uniform channels with no dead ends.This network of interconnected pores provides optimal permeability and ahigh surface area to encourage cell and tissue ingrowth,vascularization, and deposition of new bone.

The result is a novel biomaterial that, when placed next to bone ortissue, initially serves as a prosthesis and then functions as ascaffold for regeneration of normal tissues. The new biomaterialfulfills the need for an implant modality that has a preciselycontrollable shape and at the same time provides an optimal matrix forcell and bone ingrowth as well as having a high strength, inert surface.Additionally, the physical and mechanical properties of the porousstructure can be specifically tailored to the particular application athand. This new implant offers the potential for use in alveolar ridgeaugmentation, periodontics, and orthognathic reconstruction. As aneffective substitute for autografts, it will reduce the need for surgeryto obtain those grafts. It is useful in orthopedic applications as well.

Zirconium is used as the material of choice based on its good mechanicalproperties, excellent corrosion resistance, and demonstratedbiocompatibility. Additionally, zirconium has superior properties uponis oxidation to a blue-black or black oxidized zirconium. Early evidenceof excellent tissue acceptance, combined with low corrosion, has led tothe use of oxidized zirconium as a specialty surgical implant materialand its use in a variety of applications, resulting in superiorconventional and unconventional prosthetic devices.

The zirconium or zirconium alloy is deposited onto the reticulated opencell substrate prior to oxidation. In order to form continuous anduseful zirconium oxide coatings over the desired surface of the metalalloy prosthesis substrate, the zirconium alloy may have any amount ofzirconium, but preferably should contain from about 80 to about 100 wt.% zirconium, and more preferably from about 95 to about 100 wt. %.However, alloys having lesser amounts of zirconium may be used. Oxygen,niobium, and titanium include common alloying elements in the alloy withoften times the presence of hafnium. Yttrium may also be alloyed withthe zirconium to enhance the formation of a tougher, yttria-stabilizedzirconium oxide coating during the oxidation of the alloy. While suchzirconium containing alloys may be custom formulated by conventionalmethods known in the art of metallurgy, a number of suitable alloys arecommercially available. Non-limiting examples of such materials includethose consisting of zirconium with 2.5% niobium (commercially known asZircadyne 705), pure zirconium (commercially known as Zircadyne 702),and various other zirconium alloys have minor amounts of othercomponents (such as the commercial product known as Zircalloy).

Any of various deposition methods well known in the art may be used toform a surface layer of zirconium or zirconium alloy. These includechemical vapor deposition (CVD), physical vapor deposition (PVD), or acombination thereof. A CVD process may include a gaseous or liquidprecursor that contains zirconium. The precursors used may be anorganometallic type or can be an inorganic compound. The precursor isdecomposed to form metallic zirconium on the porous substrate. A PVDprocess may include evaporation of zirconium alloy in vacuum andsubsequent condensation of these vapors on to the porous substrate. Theevaporation may be carried out by heating the alloy (thus forming amelt) or by sputtering the alloy with inert gases or by arc discharge.An electrochemical deposition of zirconium alloy on to the poroussubstrates may also be accomplished by using fused salt electrolysis inwhich a zirconium salt is decomposed in order to deposit metalliczirconium onto the porous substrate.

In addition, other methods of fabrication are also possible. Physicalconstruction of a porous structure of zirconium or zirconium alloy maybe accomplished using direct casting methods known in the art.Alternatively, a cast porous structure may be coated with zirconium orzirconium alloy as described previously. Another approach forconstruction includes diffusion-bonding perforated metal layers (sheetsor plates) to build an open-cell porous structure, with the metal layerscomposed of zirconium or zirconium alloy or with the metal layerssubsequently coated with zirconium or zirconium alloy as describedpreviously. Alternatively, the porous structure may be created bysintering metallic particles or beads of zirconium or zirconium alloyusing methods known in the art, or sintering metallic particles or beadsand subsequently coating them with zirconium or zirconium alloy asdescribed previously.

Once deposited, the zirconium or zirconium alloy layer is oxidized toblue-black or black oxidized zirconium. The layer is then subjected toprocess conditions which cause the natural (in situ) formation of atightly adhered, diffusion-bonded coating of zirconium oxide on itssurface. The process conditions include, for instance, air, steam, orwater oxidation or oxidation in a salt bath. These processes ideallyprovide a thin, hard, dense, blue-black or black, low-frictionwear-resistant zirconium oxide film or coating of thicknesses typicallyon the order of several microns (10⁻⁶ meters) on the surface of theprosthesis substrate. Below this coating, diffused oxygen from theoxidation process increases the hardness and strength of the underlyingsubstrate metal.

The air, steam and water oxidation processes are described innow-expired U.S. Pat. No. 2,987,352 to Watson, the teachings of whichare incorporated by reference as though fully set forth. Additionalteachings are found in U.S. Pat. No. 5,037,438 to Davidson, theteachings of which are incorporated by reference as though fully setforth. The air oxidation process provides a firmly adherent black orblue-black layer of zirconium oxide of highly oriented monocliniccrystalline form. If the oxidation process is continued to excess, thecoating will whiten and separate from the metal substrate. The oxidationstep may be conducted in either air, steam or hot water. Forconvenience, the metal prosthesis substrate may be placed in a furnacehaving an oxygen-containing atmosphere (such as air) and typicallyheated at 700° F.-1100° F. up to about 6 hours. However, othercombinations of temperature and time are possible. When highertemperatures are employed, the oxidation time should be reduced to avoidthe formation of the white oxide.

It is preferred that a blue-black zirconium oxide layer ranging inthickness up to about 5 microns should be formed. However, largerthicknesses may be desired depending upon the particular application.For example, furnace air oxidation at 1000° F. for 3 hours will form anoxide coating on Zircadyne 705 about 4-5 microns thick. Longer oxidationtimes and higher oxidation temperatures will increase this thickness,but may compromise coating integrity. For example, one hour at 1300° F.will form an oxide coating about 14 microns in thickness, while 21 hoursat 1000° F. will form an oxide coating thickness of about 9 microns. Ofcourse, because only a thin oxide is necessary on the surface, only verysmall dimensional changes, typically less than 10 microns over thethickness of the prosthesis, will result. In general, thinner coatings(1-4 microns) have better attachment strength.

One of the salt-bath methods that may be used to apply the zirconiumoxide coatings to the metal alloy prosthesis, is the method of U.S. Pat.No. 4,671,824 to Haygarth, the teachings of which are incorporated byreference as though fully set forth. The salt-bath method provides asimilar, slightly more abrasion resistant blue-black or black zirconiumoxide coating. The method requires the presence of an oxidation compoundcapable of oxidizing zirconium in a molten salt bath. The molten saltsinclude chlorides, nitrates, cyanides, and the like. The oxidationcompound, sodium carbonate, is present in small quantities, up to about5 wt. %. The addition of sodium carbonate lowers the melting point ofthe salt. As in air oxidation, the rate of oxidation is proportional tothe temperature of the molten salt bath and the '824 patent prefers therange 550° C.-800° C. (1022° C.-1470° C.). However, the lower oxygenlevels in the bath produce thinner coatings than for furnace airoxidation at the same time and temperature. A salt bath treatment at1290° F. for four hours produces an oxide coating thickness of roughly 7microns.

Whether air oxidation in a furnace or salt bath oxidation is used, thezirconium oxide coatings are quite similar in hardness. For example, ifthe surface of a wrought Zircadyne 705 (Zr, 2-3 wt. % Nb) prosthesissubstrate is oxidized, the hardness of the surface shows a dramaticincrease over the 200 Knoop hardness of the original metal surface. Thesurface hardness of the blue-black zirconium oxide surface followingoxidation by either the salt bath or air oxidation process isapproximately 1700-2000 Knoop hardness.

Although the present invention and its advantages have been described indetail, it should be understood that various changes, substitutions andalterations can be made herein without departing from the invention asdefined by the appended claims. Moreover, the scope of the presentapplication is not intended to be limited to the particular embodimentsof the process, machine, manufacture, composition of matter, means,methods and steps described in the specification. As one will readilyappreciate from the disclosure, processes, machines, manufacture,compositions of matter, means, methods, or steps, presently existing orlater to be developed that perform substantially the same function orachieve substantially the same result as the corresponding embodimentsdescribed herein may be utilized. Accordingly, the appended claims areintended to include within their scope such processes, machines,manufacture, compositions of matter, means, methods, or steps.

1-8. (canceled)
 9. A method of making a composite material comprisingthe steps of: providing a material having a reticulated open cellstructure, depositing a layer of zirconium or zirconium alloy onto saidsubstrate; and, oxidizing said layer to blue-black or black oxidizedzirconium.
 10. The method of claim 9 wherein said step of depositingcomprises chemical vapor deposition or physical vapor deposition orboth.
 11. The method of claim 9 wherein said step of oxidizing comprisesoxidizing using air, steam, or water oxidation or any combinationthereof.
 12. The method of claim 9 wherein said step of oxidizingcomprises oxidizing in a furnace having an oxygen-containing atmosphere.13. A method of making a composite material comprising the steps of:providing a material having a reticulated open cell structure,physically constructing a layer of zirconium or zirconium alloy ontosaid substrate, and oxidizing said layer to blue-black or black oxidizedzirconium.
 14. The method of claim 13 wherein said step of physicalconstructing comprises direct casting.
 15. The method of claim 13wherein said step of physical constructing comprises building adiffusion-bonded layer. 16-21. (canceled)